Biological sensitivity determination method and system based on oxidation-reduction reaction

Abstract

The invention relates to the field of biological sensitivity determination, in particular to a biological sensitivity determination method and system based on redox reaction, and the method comprises the following steps: S1, immersing a working electrode into glucose standard solutions with different concentrations to test steady-state current, and constructing a calibration curve; s2, adding the experimental sample into a glucose standard solution with a set concentration, and monitoring a current value and sensitivity influence information in real time; s3, calculating first biological sensitivity according to the current value and the standard curve; s4, correcting the first biological sensitivity according to the sensitivity influence information; according to the method, the complex situation that the temperature and the surface pollution degree of the working electrode influence the test value of the biological sensitivity at different degrees is considered firstly, and the influence of the temperature change on the surface pollution degree of the working electrode is also considered, so that the test value of the biological sensitivity is further influenced; therefore, the accuracy of calculating the biological sensitivity is higher, so that the work of pathological analysis, drug development and the like in the later period is facilitated.

Description

Technical Field

[0001] The present invention relates to the field of biosensitivity determination, and specifically to a biosensitivity determination method and system based on redox reactions. Background Art

[0002] When testing biosensitivity based on redox reactions, as the redox reaction progresses, the surface of the working electrode will be contaminated and corroded by the generated substances, resulting in a certain degree of error in the detected current, which is not conducive to pathological analysis and drug development.

[0003] A common solution is to detect the concentrations of various substances involved in the reaction process, calculate the degree of contamination on the surface of the working electrode based on them, and then use this to correct the biosensitivity. However, this method often does not consider the dual effects of temperature on the detected current and the degree of contamination of the working electrode, so there is still a deviation in the accuracy of the corrected biosensitivity. Summary of the Invention

[0004] In view of the deficiencies of the prior art, the present invention provides a biosensitivity determination method and system based on redox reactions, which solves the technical problems in the above background art.

[0005] To achieve the above object, the present invention provides the following technical solutions: A biosensitivity determination method based on redox reactions, comprising the following steps: S1. Immerse the working electrode in glucose standard solutions of different concentrations to test the steady-state current and construct a calibration curve; S2. Add the experimental sample to a glucose standard solution with a set concentration, and monitor the current value and sensitivity influence information in real time; S3. Calculate the first biosensitivity according to the current value and the standard curve , and the first biosensitivity is used to represent the response ability of the experimental sample to the redox reaction; S4. Correct the first biosensitivity according to the sensitivity influence information to generate the second biosensitivity .

[0006] Further, in step S1, the glucose solution is diluted separately by PBS buffer solution to obtain glucose standard solutions of different concentrations, and the concentrations of the glucose standard solutions vary in a gradient manner.

[0007] Further, in step S1, the steps of constructing the calibration curve are specifically as follows: S11. Immerse the working electrode in PBS buffer solution, apply a constant potential and record the background current; S12. Use the working electrode to detect the steady-state current of each concentration of glucose standard solution. Wash the working electrode with PBS buffer between every two measurements, and then dry it with nitrogen gas. S13. Construct a coordinate system with the glucose concentration as the abscissa and the steady-state current value as the ordinate. S14. Perform linear regression using the least squares method to obtain the calculation equation of the calibration curve, and its expression is: ; In the formula, k represents the slope; b represents the intercept.

[0008] Furthermore, in step S2, the sensitivity influence information includes the glucose concentration, temperature, concentration, metal ion dissolution concentration, protein concentration, and pH value of the working electrode surface.

[0009] Furthermore, in step S3, the calculation formula of the first biological sensitivity is: ; In the formula, represents the current value; represents the current value corresponding to the glucose standard solution with a set concentration; represents the current concentration of the glucose standard solution; represents the set concentration of the glucose standard solution.

[0010] Furthermore, in step S4, it specifically includes the following steps: S41. Calculate the surface contamination degree of the working electrode according to the sensitivity influence information ; S42. Develop a biological sensitivity test experiment and record the experimental information to construct a training set; S43. Use the training set to train a long short-term memory network to obtain a target model; S44. Input the sensitivity influence information into the target model and output the first correction coefficient of the first biological sensitivity , the second correction coefficient and the third correction coefficient ; S45. Correct the first biological sensitivity according to the surface contamination degree, the first correction coefficient , the second correction coefficient and the third correction coefficient to obtain the second biological sensitivity .

[0011] Further, in step S41, it specifically includes the following steps: S411. Calculate the temperature-dependent adsorption coefficient according to the temperature in the glucose standard solution , and its calculation formula is: ; In the formula, and respectively represent the first and second influence parameters regarding ; represents the base of the natural logarithm; represents the temperature in the glucose standard solution at time t; represents the reference temperature; S412. Calculate the oxidation cumulative enhancement coefficient according to the metal ion dissolution concentration , and its calculation formula is: ; In the formula, and respectively represent the first and second influence parameters regarding ; represents the metal ion dissolution concentration in the glucose standard solution at time t; represents an infinitesimal increment of time; represents the reference metal ion dissolution concentration in the glucose standard solution; S413. Calculate the generation kinetic coefficient according to the glucose concentration and the pH value on the surface of the working electrode , and its calculation formula is: ; In the formula, represents the effective enzyme activity of glucose oxidase; represents the glucose concentration in the glucose standard solution at time t; represents the pH value of the glucose standard solution at time t; represents the acid dissociation constant of glucose oxidase; S414. Calculate the surface contamination degree of the working electrode according to the temperature-dependent adsorption coefficient , the oxidation cumulative enhancement coefficient and the kinetic coefficient , and its calculation formula is: ; In the formula, , and respectively represent the protein adsorption rate constants regarding ; represents the oxidation coefficient and the coupling coefficient of the enzymatic side reaction; represents the initial degree of the working electrode; represents the protein concentration in the glucose standard solution at time t; represents the effective specific surface area of the working electrode; represents the activation energy of the pollution reaction; represents the gas constant.

[0012] Furthermore, in step S42, the specific steps are as follows: S421. Adjust the temperature, PBS buffer concentration, pH value, and glucose concentration of the glucose test solution respectively, and conduct redox reaction biosensitivity tests respectively, and record the glucose concentration, temperature, concentration, metal ion dissolution concentration, protein concentration, and pH value on the surface of the working electrode during the test to construct a training sample; S422. After the redox reaction test is completed, calculate the third biosensitivity of each training sample ; S423. Insert a brand-new test electrode into the glucose test solution and calculate the fourth biosensitivity ; S424. Construct a biosensitivity correction formula, and its expression is: ; In the formula, , and respectively represent the first, second, and third weight coefficients of the biosensitivity correction formula at time K; represents the surface contamination value of the test electrode at time K; represents the difference between the glucose test solution at time K and the reference temperature; S425. Substitute the training sample and the corresponding third biosensitivity and the fourth biosensitivity into the biosensitivity correction formula, solve for , and and use them as sample labels.

[0013] Furthermore, in step S45, the calculation formula for the second biosensitivity is: ; In the formula, represents the first biosensitivity at time t; represents the difference between the glucose standard solution at time t and the reference temperature.

[0014] A biosensitivity measurement system based on redox reactions, comprising a preparation module, an experiment module, and a data processor; The preparation module is used to immerse a working electrode in glucose standard solutions of different concentrations to test the steady-state current and construct a calibration curve; The experiment module adds an experimental sample to a glucose standard solution with a set concentration and continuously monitors the current value and sensitivity influence information; The data processor is used to calculate the first biosensitivity based on the current value and the standard curve , and then correct the first biosensitivity according to the sensitivity influence information to generate the second biosensitivity. .

[0015] Compared with the prior art, the present invention provides a method and system for measuring biosensitivity based on redox reactions, having the following beneficial effects: 1. The present invention first takes into account that both the temperature and the surface contamination degree of the working electrode will affect the test value of biosensitivity to varying degrees, and also takes into account the influence of temperature changes on the surface contamination degree of the working electrode, and further affects the test value of biosensitivity. Therefore, the present invention has higher precision in calculating biosensitivity, which is convenient for later pathological analysis and drug development.

[0016] 2. When calculating the surface contamination degree of the working electrode, the present invention comprehensively considers these contamination sources such as protein adsorption, temperature-dependent adsorption, oxidation by-products, and enzyme side reactions, and ensures that the calculation of the surface contamination degree of the working electrode conforms to the actual changes of the glucose standard solution by adjusting the temperature-dependent adsorption coefficient, oxidation accumulation enhancement coefficient, and generation kinetic coefficient in real time. Compared with other calculation methods, the calculation precision is higher, which can effectively improve the precision of later correction of biosensitivity and is convenient for later pathological analysis and drug development. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] The drawings described herein are used to provide a further understanding of the present application and form a part of the present application. The illustrative embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation of the present application. In the drawings: Figure 1 is a flowchart of a method for measuring biosensitivity based on redox reactions according to the present invention. DETAILED DESCRIPTION

[0018] To make the above objects, features, and advantages of the present invention more apparent and understandable, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments. Thereby, the implementation process of how this application uses technical means to solve technical problems and achieve technical effects can be fully understood and implemented accordingly.

[0019] Those of ordinary skill in the art can understand that all or part of the steps in the following embodiments can be completed by instructing relevant hardware through a program. Therefore, this application can adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment combining software and hardware aspects. Moreover, this application can adopt the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk memories, CD-ROMs, optical memories, etc.) containing computer-usable program codes.

[0020] Determining the bio-sensitivity based on redox reactions is of great significance in scientific research, medical diagnosis, environmental monitoring, and industrial applications. During the determination process, in order to improve the determination efficiency, nanomaterials (such as , nanotubes) are used to modify the working electrode (such as a glassy carbon electrode) to increase the specific surface area. However, as the usage time increases, the nanomaterials will agglomerate or oxidize during long-term use (such as the carboxylation failure of carbon nanotubes), which will lead to a reduction in the effective surface area of the electrode, resulting in a gradual decrease in its sensitivity. Moreover, the measurement results will also be affected by temperature fluctuations, resulting in the measurement accuracy not meeting the expected effect. For this reason, the present invention proposes a method for determining the bio-sensitivity based on redox reactions, including the following steps: S1. Immerse the working electrode in glucose standard solutions of different concentrations to test the steady-state current and construct a calibration curve; specifically, in step S1, the glucose solution is diluted separately by PBS buffer to obtain glucose standard solutions of different concentrations, and the concentrations of the glucose standard solutions change in a gradient manner; it should be noted that the formula of the PBS buffer includes NaCl, KCl, and ; In addition, in step S1, the steps for constructing the calibration curve are specifically as follows: S11. Immerse the working electrode in the PBS buffer, apply a constant potential, and record the background current; S12. Use the working electrode to detect the steady-state current of each concentration of glucose standard solution in turn. Wash the working electrode with PBS buffer between every two measurements, and then dry it with nitrogen; S13. Construct a coordinate system with the glucose concentration as the abscissa and the steady-state current value as the ordinate; S14. Perform linear regression using the least squares method to obtain the calculation equation of the calibration curve, and its expression is: ; In the formula, k represents the slope; b represents the intercept.

[0021] S2. Add the experimental sample to the glucose standard solution with a set concentration, and monitor the current value and sensitivity influence information in real time; specifically, the experimental sample is a whole blood sample; In addition, in step S2, the sensitivity influence information includes the glucose concentration, temperature, concentration, metal ion dissolution concentration, protein concentration, and pH value on the surface of the working electrode; S3. Calculate the first biological sensitivity according to the current value and the standard curve , and the first biological sensitivity is used to represent the response ability of the experimental sample to the redox reaction; specifically, the biological sensitivity is used to represent the response ability of the biological system to the redox reaction, so it is necessary to measure the biological sensitivity according to the redox reaction of the biological system. The redox reaction of the present invention can be catalyzed by glucose oxidase (GOD) to generate gluconic acid and , and its chemical formula is as follows: ; is further reduced on the electrode surface to generate a measurable current signal (i.e., the current value). In addition, there is an electron transfer in the redox reaction on the electrode, and the current intensity is proportional to the glucose concentration. Therefore, it is necessary to detect the measurable current signal generated during the redox reaction; In addition, according to the reading corresponding to the current value in the calibration curve, the concentration change of the glucose standard solution can be directly read. Therefore, the first biological sensitivity can be calculated according to the current value and the glucose concentration of the glucose standard solution. For this reason, in step S3, the first biological sensitivity has the following calculation formula: ; In the formula, represents the current current value; represents the current value corresponding to the glucose standard solution with a set concentration; represents the current concentration of the glucose standard solution; represents the set concentration of the glucose standard solution.

[0022] S4. Correct the first biological sensitivity according to the sensitivity influence information to generate the second biological sensitivity Specifically, as the redox process progresses, more and more proteins or lipids will adsorb on the surface of the working electrode, thus affecting the current value and further affecting the detection of the first biological sensitivity. Therefore, in step S4, the following steps are specifically included: S41. Calculate the surface contamination degree of the working electrode according to the sensitivity influence information Specifically, due to various reasons, the surface of the working electrode will be contaminated, resulting in errors in the calculation of the first biological sensitivity. The reasons include: there are pores on the surface of the working electrode, which will adsorb pollutants; The free radicals (·OH) generated by decomposition will oxidize the surface of the working electrode, generating an inert oxide layer; when glucose oxidase (GOD) catalyzes glucose to produce gluconic acid and the local pH value of the glucose standard solution decreases, the corrosion of the working electrode is accelerated; due to the Arrhenius effect, for every 10-degree Celsius increase in temperature, the protein denaturation adsorption rate increases by 1.5 - 2 times. Therefore, in step S41, the following steps are specifically included: S411. Calculate the temperature-dependent adsorption coefficient according to the temperature in the glucose standard solution The calculation formula is: ; In the formula, and respectively represent the first and second influence parameters regarding ; represents the base of the natural logarithm; represents the temperature in the glucose standard solution at time t; represents the reference temperature; specifically, and are 0.01 and 0.2 respectively; is 25 degrees Celsius; S412. Calculate the oxidation cumulative enhancement coefficient according to the metal ion dissolution concentration The calculation formula is: ; In the formula, and respectively represent the first and second influence parameters regarding ; represents the metal ion dissolution concentration in the glucose standard solution at time t; represents the infinitesimal increment of time; represents the reference metal ion dissolution concentration in the glucose standard solution; specifically, and are 0.1 and 0.01 respectively; S413. Calculate according to the glucose concentration and the pH value on the surface of the working electrode Generate the kinetic coefficient , and its calculation formula is: ; In the formula, represents the effective enzyme activity of glucose oxidase; represents the glucose concentration in the glucose standard solution at time t; represents the pH value of the glucose standard solution at time t; represents the acid dissociation constant of glucose oxidase; specifically, is determined according to , for example: when , ; is 6.5; S414. Calculate the surface contamination degree of the working electrode according to the temperature-dependent adsorption coefficient , the oxidation accumulation enhancement coefficient and the kinetic coefficient , and its calculation formula is: ; In the formula, , and respectively represent the protein adsorption rate constants with respect to ; represents the oxidation coefficient and the enzyme side reaction coupling coefficient; represents the initial degree of the working electrode; represents the protein concentration in the glucose standard solution at time t; represents the effective specific surface area of the working electrode; represents the activation energy of the contamination reaction; represents the gas constant; specifically, , and are respectively , 0.12 and 0.002; is 0.03.

[0023] In step S414 of the present invention, when calculating the surface contamination degree of the working electrode, the contamination sources such as protein adsorption, temperature-dependent adsorption, oxidation by-products and enzyme side reactions are comprehensively considered, and by adjusting the temperature-dependent adsorption coefficient, oxidation accumulation enhancement coefficient and generating the kinetic coefficient in real time to ensure that the calculation of the surface contamination degree of the working electrode conforms to the actual change of the glucose standard solution. Compared with other calculation methods, the calculation accuracy is higher, which can effectively improve the accuracy of correcting the biological sensitivity in the later stage, so as to facilitate the later pathological analysis and drug development and other work.​

[0024] S42. Develop a bio-sensitivity test experiment and record the experiment information to construct a training set. Specifically, in step S42, the specific steps are as follows: S421. Adjust the temperature, PBS buffer concentration, pH value, and glucose concentration of the glucose test solution respectively, and conduct redox reaction bio-sensitivity tests respectively. Record the glucose concentration, temperature, concentration, metal ion dissolution concentration, protein concentration, and pH value on the surface of the working electrode during the test to construct training samples. Specifically, the glucose test solution is the same as the glucose standard solution, and its components only include glucose solution and PBS buffer. This redox reaction bio-sensitivity test is the same as the method in the previous steps S1 - S3. S422. After the redox reaction test, calculate the third bio-sensitivity of each training sample . Specifically, the calculation method is the same as in step S3. S423. Insert a brand-new test electrode into the glucose test solution and calculate the fourth bio-sensitivity . Specifically, the calculation method is the same as in step S3. S424. Construct a bio-sensitivity correction formula, and its expression is: ; In the formula, , and respectively represent the first, second, and third weight coefficients of the bio-sensitivity correction formula at time K. represents the surface contamination value of the test electrode at time K. represents the difference between the glucose test solution at time K and the reference temperature. Specifically, is calculated in the same way as in step S414. S425. Substitute the training samples and the corresponding third bio-sensitivity and fourth bio-sensitivity into the bio-sensitivity correction formula to solve for , and and use them as sample labels.

[0025] S43. Use the training set to train a long short-term memory network to obtain a target model. S44. Input the sensitivity influence information into the target model and output the first correction coefficient , the second correction coefficient , and the third correction coefficient and the third correction coefficient Specifically, when constructing the sample label, considering that both the temperature and the surface contamination degree of the working electrode will affect the test value of the biological sensitivity to varying degrees, and also considering the influence of temperature change on the surface contamination degree of the working electrode, which in turn affects the test value of the biological sensitivity, a complex situation, the calculation of the biological sensitivity in the present invention has higher precision, facilitating subsequent pathological analysis, drug development and other work.

[0026] S45. Correct the first biological sensitivity according to the surface contamination degree, the first correction coefficient , the second correction coefficient and the third correction coefficient to obtain the second biological sensitivity ; specifically, the calculation method of the second biological sensitivity is as shown in the biological sensitivity correction formula in step S424. In order to intuitively display the calculation method of the second biological sensitivity, in step S45, the calculation formula of the second biological sensitivity is: ; In the formula, represents the first biological sensitivity at time t; represents the difference between the glucose standard solution at time t and the reference temperature.

[0027] The above embodiments have introduced the present invention in detail. Specific examples are used in this article to elaborate on the principle and implementation of the present invention. The description of the above embodiments is only used to help understand the method and its core idea of the present invention; at the same time, for those of ordinary skill in the art, according to the idea of the present invention, there will be changes in the specific implementation and application scope. In summary, the content of this specification should not be construed as a limitation to the present invention.

Claims

1. A biosensitivity determination method based on redox reactions, characterized in that, It includes the following steps: S1. Immerse the working electrode in glucose standard solutions of different concentrations to test the steady-state current and construct a calibration curve; S2. Add the experimental sample to the glucose standard solution with a set concentration and monitor the current value and sensitivity impact information in real time; S3. Calculate the first biological sensitivity according to the current value and the standard curve , the first biological sensitivity is used to represent the response ability of the experimental sample to the redox reaction; S4. Correct the first biological sensitivity according to the sensitivity influence information to generate a second biological sensitivity .

2. The biosensitivity determination method based on redox reaction according to claim 1, wherein In step S1, the glucose solution is diluted separately by PBS buffer to obtain glucose standard solutions of different concentrations, and the concentrations of the glucose standard solutions change in a gradient manner.

3. The biosensitivity determination method based on redox reaction according to claim 1, characterized in that, In step S1, the steps for constructing the calibration curve are specifically as follows: S11. Immerse the working electrode in PBS buffer, apply a constant potential and record the background current; S12. Use the working electrode to detect the steady-state current of each concentration of glucose standard solution in turn. Clean the working electrode with PBS buffer between every two measurements, and then dry it with nitrogen; S13. Construct a coordinate system with the glucose concentration as the abscissa and the steady-state current value as the ordinate; S14. Use the least squares method for linear regression to obtain the calculation equation of the calibration curve, and its expression is: ； In the formula, k represents the slope; b represents the intercept.

4. The biosensitivity determination method based on redox reaction according to claim 1, characterized in that, In step S2, the sensitivity influence information includes the glucose concentration, temperature, concentration, metal ion dissolution concentration, protein concentration, and pH value on the surface of the working electrode.

5. The biosensitivity determination method based on redox reaction according to claim 1, wherein In step S3, the first biological sensitivity is calculated by the formula: ； Wherein, represents the current current value; represents the current value corresponding to the glucose standard solution with a set concentration; represents the current concentration of the glucose standard solution; represents the set concentration of the glucose standard solution.

6. The biosensitivity determination method based on redox reaction according to claim 1, wherein In step S4, it specifically includes the following steps: S41. Calculate the surface contamination degree of the working electrode according to the sensitivity influence information ; S42. Formulate a bio-sensitivity test experiment and record the experimental information to construct a training set; S43. Use the training set to train a long short-term memory network to obtain a target model; S44. Input the sensitivity impact information into the target model to output the first biological sensitivity of the first correction coefficient , the second correction coefficient and the third correction coefficient ; S45. Correct the first biological sensitivity according to the surface contamination degree, the first correction coefficient , the second correction coefficient and the third correction coefficient to obtain the second biological sensitivity . .

7. The biosensitivity measurement method based on redox reaction according to claim 6, characterized in that, In step S41, it specifically includes the following steps: S411. Calculate the temperature-dependent adsorption coefficient based on the temperature in the glucose standard solution , and its calculation formula is as follows: ； In the formula, and respectively represent the first and second influence parameters with respect to ; represents the base of the natural logarithm; represents the temperature in the glucose standard solution at time t; represents the reference temperature; S412. Calculate the oxidation cumulative enhancement factor based on the metal ion dissolution concentration , and its calculation formula is: ； In the formula, and respectively represent the first and second influence parameters with respect to ; represents the metal ion dissolution concentration in the glucose standard solution at time t; represents an infinitesimal increment of time; represents the reference metal ion dissolution concentration in the glucose standard solution. S413. Calculate according to the glucose concentration and the pH value on the surface of the working electrode to generate a kinetic coefficient , and its calculation formula is: ； In the formula, represents the effective enzyme activity of glucose oxidase; represents the glucose concentration in the glucose standard solution at time t; represents the pH value of the glucose standard solution at time t; represents the acid dissociation constant of glucose oxidase; S414. Calculate the surface contamination degree of the working electrode according to the temperature-dependent adsorption coefficient , the oxidation accumulation enhancement coefficient and the kinetic coefficient , and its calculation formula is: , the calculation formula is as follows: ； In the formula, , and respectively represent the protein adsorption rate constants with respect to ; represents the oxidation coefficient and the enzyme side reaction coupling coefficient; represents the initial degree of the working electrode; represents the protein concentration in the glucose standard solution at time t; represents the effective specific surface area of the working electrode; represents the activation energy of the pollution reaction; represents the gas constant.

8. The biosensitivity determination method based on redox reaction according to claim 6, characterized in that, In step S42, the specific steps are as follows: S421. Adjust the temperature, PBS buffer concentration, pH value, and glucose concentration of the glucose test solution respectively, conduct biosecnsitivity tests for redox reactions respectively, and record the glucose concentration, temperature, concentration, metal ion dissolution concentration, protein concentration, and pH value on the surface of the working electrode to construct training samples; S422. After the redox reaction test, calculate the third biological sensitivity of each training sample ; S423. Insert a brand-new test electrode into the glucose test solution and calculate the fourth biological sensitivity ; S424. Construct a bio-sensitivity correction formula, and its expression is: ； Wherein, , and respectively represent the first, second, and third weight coefficients of the biosensitivity correction formula at time K; represents the surface contamination value of the test electrode at time K; represents the difference between the glucose test solution and the reference temperature at time K; S425. Substitute the training samples and the corresponding third biological sensitivity and the fourth biological sensitivity into the biological sensitivity correction formula to solve for , and and use them as sample labels.

9. The biosensitivity determination method based on redox reaction according to claim 6, characterized in that, In step S45, the second biological sensitivity is calculated by the formula: ； In the formula, represents the first biological sensitivity at time t; represents the difference between the glucose standard solution at time t and the reference temperature.

10. A system for implementing the redox reaction-based biological sensitivity assay method according to any one of claims 1-9, characterized in that, It includes a preparation module, an experimental module and a data processor; The preparation module is used to immerse the working electrode in glucose standard solutions of different concentrations to test the steady-state current and construct a calibration curve; The experimental module adds the experimental sample to the glucose standard solution with a set concentration and monitors the current value and sensitivity impact information in real time for; The data processor is used to calculate a first biological sensitivity according to a current value and a standard curve , and then correct the first biological sensitivity according to sensitivity influence information to generate a second biological sensitivity .

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